Apparatus and methods for assessment of neuromuscular function

ABSTRACT

Apparatus and methods are provided for the assessment of neuromuscular function. Using an apparatus of the invention, stimuli are applied to a nerve that traverses the wrist of an individual. The stimuli are applied at a point that is proximal to the wrist. Stimulation of the nerve causes a muscle innervated by that nerve to respond. The muscle response generates a myoelectric potential, which is detected by an apparatus of the invention at a point that is proximal to the wrist. The delay between stimulation of a nerve and detection of a muscular response to that stimulation is processed to indicate an assessment of neuromuscular function. For example, a sufficient delay between application of stimulus and muscle response may indicate the presence of Carpal Tunnel Syndrome.

FIELD OF THE INVENTION

The invention relates to apparatus and methods for assessment ofneuromuscular function. More specifically, the invention relates toapparatus and methods for diagnosing peripheral nerve and musclepathologies based on assessments of neuromuscular function.

BACKGROUND OF THE INVENTION

There are many clinical and non-clinical situations that call for arapid, reliable and low-cost assessments of neuromuscular function.Reliable and automated devices are needed to monitor neuromuscularfunction in surgical and intensive care settings. For example, musclerelaxants significantly improve surgical procedures and post-operativecare by regulating the efficacy of nerve to muscle coupling through aprocess called neuromuscular blockade. They are, however, difficult touse in a safe and effective manner because of the wide variation andlack of predictability of patient responses to them. In another setting,an easy to use and reliable indicator would be beneficial in assessingpotential contamination exposure situations by chemical agents. Theseagents disrupt neuromuscular function and effectively causeneuromuscular blockage, putting soldiers and civilians at risk.

The most common causes of neuromuscular disruption are, however, relatedto pathologies of the peripheral nerves and muscles. Neuromusculardisorders, such as, for example, Carpal Tunnel Syndrome (CTS), are verycommon and well known to the general public. Despite their extensiveimpact on individuals and the health care system, detection andmonitoring of such neuromuscular pathologies remains expensive,complicated, and highly underutilized.

CTS is one of the most common forms of neuromuscular disease. Thedisease is thought to arise from compression of the Median nerve as ittraverses the wrist. CTS often causes discomfort or loss of sensation inthe hand, and, in severe cases, a nearly complete inability to use one'shands. Highly repetitive wrist movements, as well as certain medicalconditions, such as, for example, diabetes, rheumatoid arthritis,thyroid disease, and pregnancy, are thought to be factors thatcontribute to the onset of CTS. In 1995, the US National Center forHealth Statistics estimated that there were over 1.89 million cases ofCTS in the United States alone.

Effective prevention of CTS requires early detection and subsequentaction. Unfortunately, the state of CTS diagnosis is rather poor. Evenexperienced physicians find it difficult to diagnose and stage theseverity of CTS based on symptoms alone. The only objective way todetect CTS is to measure the transmission of neural signals across thewrist. The gold standard approach is a formal nerve conduction study bya clinical neurologist, but this clinical procedure has a number ofimportant disadvantages. First, it is a time consuming process thatrequires the services of a medical expert, such as a neurologist.Second, the procedure is very costly (e.g., $600-$1000). Furthermore, itis not available in environments where early detection couldsignificantly decrease the rate of CTS, such as the workplace where asignificant number of causes of CTS appear. As a result of thesedisadvantages, formal electrophysiological evaluation of suspected CTSis used relatively infrequently, which decreases the likelihood of earlydetection and prevention.

The prior art reveals a number of attempts to simplify the assessment ofneuromuscular function, such as in diagnosing CTS, and to make suchdiagnostic measurements available to non-experts. Rosier (U.S. Pat. No.4,807,643) describes a portable device for measuring nerve conductionvelocity in patients. This instrument has, however, several veryimportant disadvantages. First, it requires placement of two sets ofelectrodes: one set at the stimulation site and one set at the detectionsite. Consequently, a skilled operator with a fairly sophisticatedknowledge of nerve and muscle anatomy must ensure correct application ofthe device. Inappropriate placement of one or both of the electrode setscan lead to significant diagnostic errors. Second, the Rosier apparatussuffers from the disadvantage that it is not automated. In particular,it demands that the user of the device establish the magnitude of theelectrical stimulus, as well as a response detection threshold. Theseparameters are difficult to determine a priori, and their rapid andcorrect establishment requires an advanced understanding of bothneurophysiology and the detailed electronic operation of the apparatus.

Spitz, et al. (U.S. Pat. No. 5,215,100) and Lemmen (U.S. Pat. No.5,327,902) have also attempted to enhance the earlier prior art.Specifically, they proposed systems that measure nerve conductionparameters between the arm or forearm and the hand, such as would berequired for diagnosing CTS. In both cases, however, electrodesupporting structures or fixtures were proposed that would substantiallyfix the positions at which the stimulation electrodes contact the armand the detection electrodes contact the hand. Furthermore, thesesystems suffer, from several important disadvantages. First, bothsystems are rather large and bulky, because they include a supportingfixture for the arm and hand of an adult. This severely limits theirportability and increases their cost. Second, these devices stillrequire highly trained operators who can make the appropriateadjustments on the apparatus so as to insure electrode contact with theproper anatomical sites on the arm and hand. A third disadvantage ofboth systems is that they continue to demand multiple operator decisionsregarding stimulation and detection parameters. Finally, these prior artsystems suffer from the disadvantage that they do not automaticallyimplement the diagnostic procedure and indicate the results in a simpleand readily interpretable form.

There remains a need, therefore, for apparatus and methods for assessingneuromuscular function that are less time consuming, less expensive, andmore available to a wider range of the general public (i.e., are moreportable and easy to use). Such apparatus and methods are needed toprovide more widespread early detection and prevention of neuromuscularpathologies, such as CTS. The present invention addresses these needs.

SUMMARY OF THE INVENTION

In accordance with the invention, apparatus and methods are provided forthe substantially automated, rapid, and efficient assessment ofneuromuscular function without the involvement of highly trainedpersonnel. Assessment of neuromuscular function occurs by stimulating anerve, then measuring the response of a muscle innervated by that nerve.The muscle response is detected by measuring the myoelectric potentialgenerated by the muscle in response to the stimulus. One indication ofthe physiological state of the nerve is provided by the delay betweenapplication of a stimulus and detection of a muscular response. If thenerve is damaged, conduction of the signal via the nerve to the muscle,and, hence, detection of the muscle's response, will be slower than in ahealthy nerve. An abnormally high delay between stimulus application anddetection of muscle response indicates, therefore, impairedneuromuscular function. In apparatus and methods of the invention, boththe application of stimulus and the detection of responses is carriedout entirely at a position that is immediately proximal to the wrist ofan individual (i e., the wrist crease). This anatomical location isfamiliar and easy to locate, thus ensuring correct placement of theapparatus at the assessment site by non-experts while still maintainingthe accuracy of results. This ease of use increases the availability anddecreases the cost of diagnosing pathologies such as Carpal TunnelSyndrome (CTS).

Apparatus and methods of the invention assess neuromuscular function inthe arm of an individual by using a stimulator to apply a stimulus to anerve that traverses the wrist of the individual. The stimulator isadapted for applying the stimulus to the nerve at a position which isproximal to the wrist of the individual. The stimulus may be, forexample, an electrical stimulus or a magnetic stimulus. Other types ofstimuli may be used. A detector, adapted for detecting the myoelectricpotential generated by a muscle in response to the stimulus, detects theresponse of the muscle to the stimulus at a site that is also proximalto the wrist of the individual. A controller then evaluates thephysiological function of the nerve by, for example, determining a delaybetween application of stimulus and detection of myoelectic potential.The delay is then correlated to the presence or absence of aneuromuscular pathology, such as, for example, Carpal Tunnel Syndrome(CTS).

In a preferred embodiment, the stimulator and the detector are both inelectrical communication with electrodes adapted for placement on thearm of an individual proximal to the wrist. The controller may also bein electrical communication with a reference electrode and a temperaturesensor. An apparatus of the invention may further comprise acommunications port for establishing communication between the apparatusand an external device, such as, for example, a personal computer.

In another embodiment, an apparatus of the invention further comprisesan indicator. The indicator is in electrical communication with thecontroller and is adapted for indicating the physiological functionevaluated by the controller in response to the stimulus applied andmyoelectic potential detected. The indicator may comprise a lightemitting diode. In a particularly preferred embodiment, the indicator isadapted for indicating the presence or absence of CTS.

An apparatus of the invention may be further embodied in an electrodeconfiguration contained in an electrode housing for releasably securingto the wrist of an individual. The electrode housing contains anattachment mechanism, such as, for example, a non-irritating adhesivematerial, for securing to the arm of the individual and may bedisposable. The electrode housing preferably has a connector forelectrical communication with an apparatus comprising a stimulator, adetector, and a processor, as described above.

The electrode housing comprises stimulation and detection electrodes.The stimulation and detection electrodes are sized and shaped in thehousing so that they contact an anterior aspect of an arm of theindividual proximal to the wrist, when the housing is secured to thewrist of the individual. The electrode configuration may further containa temperature sensor and/or a reference electrode.

In a preferred embodiment, the electrode configuration comprises asecond stimulation electrode and a second detection electrode. The twostimulation electrodes are positioned substantially in the center of theelectrode housing and are arranged so that they are positioned atopposite ends of the housing. The two stimulation electrodes arepreferably arranged so that, when the housing is placed on the anterioraspect of an arm of a user, one of the stimulation electrodes is locatedimmediately proximal to the wrist and the other at a location moreproximal from the wrist. The two detection electrodes are also locatedat opposite ends of the housing, but they are positioned such that, whenplaced on the anterior aspect of an arm of a user, one detectionelectrode is located on the medial, and the other on the lateral, sideof the wrist.

Methods of the invention relate to the assessment of neuromuscularfunction using an apparatus of the invention. Using an apparatus, asdescribed above, a stimulus is applied to a nerve that traverses thewrist of an individual proximal to the wrist. A muscle innervated by thenerve responds and thereby generates a myoelectric potential, which isdetected proximal to the wrist of the individual. The detected responseis processed by determining a first derivative of the myoelectricpotential and, preferably, a second derivative of the myoelectricpotential. In a preferred embodiment, these derivatives are used todetermine an appropriate stimulation level, as well as to determine thedelay between application of stimuli and detection of the associatedresponses. In another embodiment, additional measurements related to thedelay are taken. For example, changes in the delay induced byapplication of at least two stimulus applications is determined. Thedelay and associated parameters calculated from any of the measurementsare then correlated to a physiological function of the nerve and muscle.

In preferred embodiments, an apparatus of the invention is used toindicate the presence or absence of CTS. A plurality of stimuli areapplied to a nerve passing through the carpal tunnel, such as, forexample, the Median nerve. The stimuli may be delivered one at a time ata predetermined rate or they may be delivered in pairs at apredetermined rate. If delivered in pairs, the application of stimuli isseparated by a predetermined time interval.

A plurality of myoelectric potentials are generated by a muscleinnervated by the stimulated nerve in response to the stimuli. Eachmyoelectic potential is generated in response to a respective stimulusapplication. A delay for each of said stimulus applications and detectedresponses is determined. Statistics such as, for example, mean andstandard deviation, are calculated for the plurality of delays. Theprobable value that the individual has CTS is calculated based on thesestatistics. An indication of the presence or absence of CTS is thengiven based on that value.

In other embodiments of the invention, the method may involve furthersteps. For example, in one embodiment of the invention, the methodrelates to calculating the difference between delays measured inresponse to two stimuli delivered at short temporal intervals, anddetermining the probable value that an individual has CTS based on thesedelay differences and calculated statistics, as described above. Inanother embodiment, a level of noise is measured prior to stimulatingthe nerve. In yet another embodiment, the mean and standard deviation ofthe delays is adjusted relative to the skin temperature.

An apparatus and method for the essentially automated and accurateassessment of neuromuscular function is therefore provided. Theapparatus and methods of the invention allow for the less costly andmore readily available detection of neuromuscular pathologies, such as,for example, CTS, without the aid of a skilled professional.

The invention will be understood further upon consideration of thefollowing drawings, description, and claims.

DESCRIPTION OF THE DRAWINGS

FIG. 1 is an illustration of an embodiment of the apparatus of theinvention attached to the wrist of a user.

FIG. 2A shows a top surface of the embodiment of the apparatus of theinvention shown in FIG. 1.

FIG. 2B illustrates a bottom surface of the embodiment of the apparatusof the invention shown in FIG. 1 depicting an electrode configuration.

FIG. 3 is a block diagram of an embodiment of the apparatus of theinvention.

FIG. 4 illustrates electronic circuitry for an embodiment of anapparatus of the invention.

FIG. 5 is a graph showing a muscle response evoked and measured by anapparatus of the invention.

FIG. 6 is a graph showing a second derivative of a muscle responsesignal evoked and measured by an apparatus of the invention.

FIG. 7 is flow chart of an embodiment of an algorithm for detectingcarpal tunnel syndrome using an apparatus of the invention.

DETAILED DESCRIPTION OF THE INVENTION

An illustrative embodiment of an apparatus of the invention and itsplacement on the users forearm 8 is shown in FIG. 1. The inventionconsists of two major components: a neuromuscular electrode 1 and anelectronic monitor 2. The neuromuscular electrode 1 includes both astimulator and a detector. The electronic monitor 2 includes both acontroller and an indicator. In this embodiment, the neuromuscularelectrode 1 and electronic monitor 2 are physically separable withelectrical connections between the two components established byphysical contact between a connector 6, associated with theneuromuscular electrode 1 and connector slot 7 associated with theelectronic monitor 2. In another embodiment, neuromuscular electrode 1and electronic monitor 2 constitute a single, physically inseparableunit. The electronic monitor 2 contains means to actuate the diagnosticprocess. Referring to the illustrative embodiment shown in FIG. 1, apushbutton 3 is provided to initiate said diagnostic process. Theelectronic monitor 2 also contains an indicator to display or convey theresults of the diagnostic process. Referring to the illustrativeembodiment shown in FIG. 1, an indicator includes a display 4, whichincludes two multi-segment light-emitting diodes (LEDs) and whichprovides feedback and results. Other indicators may be used, including,but not limited to, single and multicolor discrete LEDs. Other types ofindicators, such as, for example, speakers, may provide auditorysignals. The electronic monitor 2 also contains a communications port toconnect and communicate with external devices. Referring to theillustrative embodiment shown in FIG. 1, the communications portincludes a jack 5 into which a cable may be inserted. The other end ofthe cable is then connected to any number of different devices,including, but not limited to, computers and telephone lines.

The neuromuscular electrode 1 delivers electrical stimuli to the skinsurface, detects biopotentials from the skin surface and measuresadditional physiological and biological parameters, such as, forexample, skin temperature. As shown in FIG. 1, the neuromuscularelectrode 1 is placed on the anterior aspect of the forearm 8immediately proximal to the wrist crease 9. In the preferred embodiment,the physical dimensions of the neuromuscular electrode 1 are chosen froma predetermined set of dimensions which are optimized for the range ofwrist sizes found in adults. For example, the electrodes may beconfigured in a small, regular and large size. Additional embodimentsare contemplated in which the neuromuscular electrode 1 includes meansto vary its physical dimensions over a predetermined range, such as, forexample, being contained in an electrode housing, such as, an adjustableband or strap. The band or strap may also be detachable.

An illustrative embodiment of the neuromuscular electrode 1 is shown inFIG. 2A. FIG. 2A shows the top surface of the neuromuscular electrode 1and its proper location on the user's wrist. In one embodiment, the topsurface of the neuromuscular electrode 1 contains printed instructions46 and/or other visual indications 45 to help the user properly positionit. FIG. 2B shows the bottom surface of the neuromuscular electrode 1.The illustrative configuration allows muscle activity in the Thenarmuscle group 51 to be evoked and sensed when the neuromuscular electrode1 is positioned immediately proximal to the wrist crease 9, as shown inFIG. 2A. Two bioelectrical transduction sites, 30 and 31, hereafterreferred to as the stimulation sites, are positioned approximatelymidway between the lateral end 19 and medial end 17 of the neuromuscularelectrode 1. The two stimulation sites, 30 and 31, are arranged in adistal to proximal line such that one of the sites is near the distalend 18 of the neuromuscular electrode 1 and one of the sites is near theproximal end 20 of the neuromuscular electrode 1.

The stimulation sites may consist of stimulation electrodes comprised ofdelineated areas of bioelectrical signal transduction means that convertelectronic signals into electrochemical ones and vice versa. In apreferred embodiment, these sites are composed of a plurality of layersof different materials with substantially the same area. A first layeris directly attached to the bottom face of the neuromuscular electrode 1and is preferably formed by a thin layer of silver. A second layer isattached to first layer and preferably consists of a silver-chloridesalt. A third layer is attached to second layer and contacts the user'sskin on its exposed surface. The third layer is preferably composed ofan electrolyte hydrogel, such as, for example, sodium chloride.

When the neuromuscular electrode 1 is properly positioned as shown inFIG. 2A, the two stimulation sites, 30 and 31, will overlie the Mediannerve 50. The nerve 50 is stimulated by passing a low amplitude current(e.g., typically less than 10 milliamps) through the two stimulationsites, 30 and 31. The current is provided by an external sourceelectrically coupled to contacts, 34 and 35, on the external connector6. The contacts, 34 and 35, and the stimulation sites, 30 and 31, arecoupled by electrically conductive and insulated means, 32 and 33.

Two transduction sites, 21 and 22, hereafter referred to as thedetection sites, are positioned at the extreme lateral end 19 and medialend 17 of the neuromuscular electrode 1 near its proximal end 18. In apreferred embodiment, the detection sites, 21 and 22, consist ofdetection electrodes comprised of delineated areas of bioelectricalsignal transduction means that convert electronic signals intoelectrochemical ones and vice versa. In a preferred embodiment, thesesites are constructed in a substantially similar manner to thestimulation sites, 30 and 31.

Contraction of the Thenar muscles 51 will generate a myoelectricpotential and create a bioelectrical potential difference between thelateral 21 and medial 22 detection sites due to the relative proximityof the lateral detection site 21 to the Thenar muscles 51. Thispotential difference may be measured as a small (e.g., typically lessthan 0.5 mV) differential voltage between contacts, 25 and 26, on theexternal connector 6. The contacts, 25 and 26, and the detection sites,21 and 22, are coupled by electrically conductive and insulated means,23 and 24. The measurement of the differential voltage signal isenhanced by the availability of a reference potential, which is providedby transduction site 27, hereafter referred to as the reference site, orreference electrode. This site is positioned along the medial end 17 ofthe neuromuscular electrode 1 towards its proximal end 20. The positionof the reference site 27 is, however, not critical and has relativelylittle effect on the function of the invention. In a preferredembodiment, the reference site 27 is constructed in a substantiallysimilar manner to the stimulation sites, 30 and 31, and detection sites,21 and 22. The reference potential is made available at a contact 29 onthe external connector 6, which is coupled to the reference site 27 byelectrically conductive and insulated means 28.

The neuromuscular electrode 1 contains a temperature sensor 36, such as,for example, a DS1820(Dallas Semiconductor, Dallas, Tex.) or athermistor. The temperature sensitive part of the sensor 36 contacts theusers skin directly or indirectly through an intermediary material thatefficiently conducts heat. The temperature sensor 36 can be placed atany available location within the area of the neuromuscular electrode 1.The temperature sensor 36 is powered and transmits temperatureinformation to electronic monitor 2 through two or more contacts, 39 and40, on the external connector 6. The contacts, 39 and 40, and thetemperature sensor 36 are coupled by electrically conductive andinsulated means, 37 and 38.

Additional configurations and arrangements of transduction sites andsensors have been contemplated and should be considered within the scopeof the present invention. One such configuration utilizes a single pairof transduction sites for both stimulation and detection throughelectronic multiplexing.

The electronic monitor 2 has a number of functions. The monitor 2detects, amplifies, processes and stores bioelectrical potentials, suchas those generated by nerve or muscle activity. It also generatesstimuli, such as steps of electrical current, with sufficient magnitudeto trigger impulses in nerves or muscles. In addition, it communicateswith the user and with external instruments, such as, for example, apersonal computer. Finally, the electronic monitor 2 includes acontroller to process data and control the intensity and duration ofstimulus applications.

An illustrative block diagram of the electronic monitor 2 of FIG. 1 isshown in FIG. 3. Differential amplifier 60 amplifies the voltagedifference between the input terminals and generates a voltage that isproportional to that voltage difference. When the electronic monitor 2and neuromuscular electrode 1 of FIG. 1 are connected by physicalcontact between connectors, 6 and 7, the differential amplifier 60 ofFIG. 3 is electrically coupled to detection sites, 21 and 22, andreference site 27. Since the bioelectrical signals from the body surfacetypically have a source impedance between about 5 KΩ to about 50 KΩ andcontain large common mode signals, the differential amplifier 60 musthave a high input impedance, a good common mode rejection ratio and alow leakage current. These requirements are preferably met by aninstrumentation amplifier, such as, for example, the INA111 (Burr-Brown,Tuscon, Ariz.) or the AD621 (Analog Devices, Norwood, Mass.)

The differential amplifier 60 is electrically coupled to a signalconditioning unit 61 that prepares the signal for analog-to-digitalconversion and subsequent processing. The signal conditioning unit 61preferably removes DC offsets, amplifies, low-pass filters, and createsa DC bias. The signal conditioning unit 61 is electrically coupled to ananalog-to-digital converter on the controller 63.

Temperature sensor interface electronics 62 power the temperature sensorand convert temperature related signals into a form interpretable bycontroller 63. Stimulator 64 generates an electrical impulse with eitheror both of the magnitude and duration of the impulse being determined bysignals from controller 63.

The stimulator 64 is preferably embodied by a circuit which gates thedischarge of a capacitor charged to a high voltage (e.g., 100 volts).The capacitance value (e.g., 1 μF is chosen so that the discharge timeconstant (e.g., several seconds) is much longer than the typical impulseduration (e.g., less than 1 millisecond). The voltage across thecapacitor is established by internal charging means, such as, forexample, a DC-DC converter. In another embodiment, it is established byexternal charging means. In the later case, the stimulator 64 is capableof generating a finite number of electrical impulses before it has to berecharged by the external charging means.

Actuating means 65 are electrically coupled to processor 63 andpreferably embodied by one or more push button switches. Indicator 66 isalso electrically coupled to controller 63 and preferably embodied in asingle, or multi-segment, LED. Finally, external interface 67 iselectrically coupled to controller 63 and preferably embodied as astandard RS-232 serial interface. The controller 63 performsanalog-to-digital conversion, senses and controls I/O lines, andprocesses, analyzes and stores acquired data. The controller 63 ispreferably embodied as a single, integrated, low-cost embeddedmicrocontroller. However, in other embodiments, the controller 63 isconfigured with multiple components, such as, for example, amicroprocessor and external components that perform analog-to-digitalconversion and other necessary functions.

FIG. 4 shows a schematic diagram of the circuitry of one embodiment ofthe electronic monitor 2 of FIG. 1. The illustrative circuit of FIG. 4includes a detection sub-circuit, a stimulation sub-circuit and acontrol and processing sub-circuit. The detection stage is based onamplifer U1, a type INA111 (Burr-Brown, Tucson,Ariz.) instrumentationamplifier. Each of a pair of inputs of amplifier U1, 100 and 101, iselectrically coupled to one of the detector sites, 21 and 22, of FIG.2B. In addition, amplifier U1 has a reference pin 102 at which itreceives a reference potential through electrical coupling to referencesite 27 of FIG. 2B. U1 is a monolithic instrumentation amplifier andrequires one external component, a resistor, R7, to establish itsamplification gain, which is preferably a factor of 10. Amplifier U1 ispowered by a two sided symmetrical power supply providing +Vc 110 and-Vc 111 (e.g., 6 volts), as well as a ground 112. In a preferredembodiment,+Vc 110,Vc 111, and the ground 112 are provided by twobatteries, B1 and B2, connected in series, as shown in FIG. 4. Theoutput of amplifier U1 is coupled through a high pass filter formed bycapacitor C1 and resistor R1 to the input of a non-inverting amplifierformed by operational amplifier U2a. The high pass filter removes any DCoffset in the output of amplifier U1. In a preferred embodiment,capacitor C1 and resistor R1 are chosen for a high pass corner frequencyof about 2 Hz. The gain of the non-inverting amplifier is established byresistors R2 and R10 and is preferably set to a gain of 500. The outputof first operational amplifier U2a is coupled to input of secondoperational amplifier U2b by a low pass filter formed by resistor R3 andcapacitor C2. The low pass filter removes high frequency noise from thesignal. In a preferred embodiment, resistor R3 and capacitor C2 arechosen for a low pass corner frequency of about 3 KHz. The secondoperational amplifier U2b is configured simply as an impedance buffer.The output of amplifier U2b is coupled to an analog-to-digitalconversion pin on microcontroller U4 by a DC biasing circuit consistingof capacitor C4, along with resistors R8 and R9. The purpose of the DCbiasing circuit is to insure that all signals vary from ground 112 to+Vc 110, since the analog-to-digital conversion electronics ofmicrocontroller U4 operate only on positive voltages. The detectionstage also has a combination communication and power line 116, forinterfacing to a "one-wire" temperature sensor 36 of FIG. 2B, connectedto an I/O pin on microcontroller U4.

The stimulation sub-circuit of the apparatus is based on energy storagecapacitor C3, which is a high capacitance (e.g., 1 μF or greater) andhigh voltage (e.g., greater than 100 volts) capacitor. In one embodimentof the apparatus, capacitor C3 is charged to greater than 100 volts byan external charging means 105. Capacitor C3 charging is accomplished bycharging means 105, which passes electrical current between terminals107 and 106, which are temporarily electrically coupled to capacitor C3terminals 109 and 108 during the charging period. Once capacitor C3 ischarged, charging means 105 is removed. Electrical stimulation of nerveand muscle is accomplished by discharging capacitor C3 through leads 103and 104, which are electrically coupled to stimulation sites, 30 and 31.Control of stimulation duration is provided by a power MOSFET transistorQl, which gates discharge according to a digital signal frommicrocontroller U4. Resistor R4 protects transistor Qi by limiting thecurrent that flows through it.

The control and processing stages of the apparatus are based onmicrocontroller U4, which is preferably a type PIC 12C71 (MicroChip,Chandler, Ariz.) microcontroller. U4 provides processing and storagecapabilities, analog-to-digital conversion and input/output control. Inaddition to the aforementioned connections to detection and stimulationsubcircuits, microcontroller U4 detects depression of switch S1, whichis connected to an I/O pin and controls light emitting diode LED1, whichis also connected to an I/O pin. Resistor R6 limits current into the I/Opin when switch S1 is depressed and resistor R5 limits current throughthe light-emitting diode LED1. In addition, serial communication 115 toexternal devices is provided by the remaining available I/O pin. Controland processing algorithms are stored in microcontroller U4 and executedautomatically upon application of power. Other electronic circuitry maybe used to perform the processes described above and is considered to bewithin the scope of the invention. One skilled in the art knows how todesign electronic circuitry to perform the functions outlined above.

A major object of the present invention is to serve as a detectionsystem for CTS. Conventional detection of CTS is based on an analysis ofcertain features of the evoked muscle response, typically the distalmotor latency (DML). The DML represents the time lag between stimulationof the Median nerve 50 immediately proximal to the wrist crease 9 andarrival of the neurally conducted impulse at the Thenar muscle group 51after traversing the Carpal Tunnel. One of the most common andconsistent indications of CTS is an increase in the DML. Although thereis no single definition for the DML, it is generally defined as theamount of time that elapses between the start of the stimulus (i.e.,time =0) and the occurrence of a consistent feature on the muscleresponse.

A typical muscle response 120, evoked and acquired using an apparatus ofthe invention, is shown in FIG. 5. The vertical scale 121 indicates theamplitude of the muscle response in millivolts as measured betweendetection sites 21 and 22. The horizontal scale 122 indicates theelapsed time from the onset of the stimulation pulse (i.e., stimulusoccurred at time =0). The large signal transients 123 that occur in thefirst 2 milliseconds represent stimulus associated artifacts and areunrelated to activity in the Thenar muscles 51. An evoked muscleresponse 120 may be characterized by many parameters including, but notlimited to, a time to onset 124, a time to peak 125, a peak amplitude126, a peak to peak amplitude 127 and a peak to peak width 128. In theillustrative example of FIG. 5, the time to onset 124 is about 3.7milliseconds, and the time to peak 125 is about 5.8 milliseconds.

Because detection of the Thenar muscle 51 response occurs at asignificant distance from its physiological site of origin, theintervening tissue acts as a low pass filter. This results in amplitudeattenuation and temporal spreading of the detected waveform as comparedto measurements taken directly over the Thenar muscles 51. The decreasein amplitude results in a reduction in the signal-to-noise ratio of thedetected muscle response 120. The temporal spreading obscures sharpcharacteristic features of the response 120. Taken together these twolow-pass related effects make a consistent and accurate identificationof muscle response features, such as the time to onset 124 or the timeto peak 125, difficult and highly variable, especially in the presenceof various noise sources (e.g., extraneous muscle activity such as wouldbe caused by a muscle twitch in an arm muscle).

In a preferred embodiment, analysis of the muscle response 120 issignificantly enhanced by preprocessing it prior to determination of itscharacteristic features. One such preprocessing step is to take thesecond derivative of the muscle response 120 as shown in FIG. 6. Theadvantageous nature of this preprocessing step is evident from the factthat the second derivative 130 (solid line) has a peak 131 near theonset 124 of the muscle response 120. Consequently, it is possible toaccurately and consistently obtain a latency estimate 133 by simplydetecting the presence of this peak 131. By contrast, a directestimation of the time to onset 124 from the muscle response 120requires establishment of an arbitrary voltage threshold which may varysignificantly among different individuals.

In a preferred embodiment, the sharp peak 131 in the second derivative130 of FIG. 6 is obtained by first smoothing the muscle response 120,such as by, for example, convolving it with a normalized. Gaussianwaveform with a predetermined standard deviation. Subsequently, thefirst derivative is calculated by estimating the instantaneous slope foreach data point in the muscle response 120. The second derivative isthen calculated by estimating the instantaneous slope for each datapoint in the just computed first derivative. In order to conservedynamic memory resources, the first and second derivatives 130 can besequentially calculated for small sections of the muscle response 120and the values discarded if they do not indicate the presence of a peak131 in the second derivative 130.

Once the peaks 131 in the second derivative 130 have been identified,the largest positive peak within a defined time window 136 is selected.This time window 136 is defined as occurring between two time limits,134 and 135. In a preferred embodiment, the lower time limit 134 ispredetermined and reflects the amount of time required for artifacts 123associated with the stimulus to decay to an amplitude that issignificantly less than the amplitude of the actual signal evoked fromthe muscle 120. The lower time limit 134 is preferably about 2.5milliseconds. Other lower time limits may, however, be used. Inaddition, it is possible to dynamically establish the lower time limit134 by analyzing the amplitude decay of the stimulus associated artifact123. The upper time limit 135 is determined dynamically. In a preferredembodiment, the upper time limit 135 is set to reflect the time duringwhich the first derivative of the evoked muscle response 120 ispositive. In other words, it reflects the period of time during whichthe evoked muscle response 120 is increasing. By establishing the uppertime limit 135 in this fashion, large peaks 132 in the second derivativeof the response 130, which occur in the latter portion of the response,are ignored and, therefore, do not result in incorrect estimates of thelatency 133.

In accordance with a preferred embodiment of the present invention, FIG.7 shows an illustrative algorithm for detecting CTS using an apparatusof the invention in an entirely automated fashion. The algorithmcommences in process step 140 by activation of actuating means 65, suchas, for example, by depression of a START switch S1. If the actuationmeans have been activated, the algorithm continues with process step142. Otherwise process step 140 is continuously executed until theactuating means are activated. In process step 142, the root-mean-square(RMS) value of the noise is obtained in the absence of any electricalstimulation and compared against a predetermined threshold, n_(max). Ifthe noise RMS is less than n_(max), the algorithm continues with processstep 146. However, if the noise RMS is greater than n_(max), thealgorithm proceeds to process step 144, in which indicator 66 is used toindicate a problem with the noise level to the user. Subsequently, thealgorithm returns to process step 140 and waits for reactivation of theSTART switch S1.

In process step 146, the magnitude of stimuli to be used in diagnosingCTS is determined. In a preferred process, this parameter is determinedautomatically without user involvement. This is accomplished bygradually increasing the stimulation duration in predeterminedincrements (e.g., 25 microseconds) until the evoked muscle response 120meets one or more predetermined criteria. As an illustrative example,the stimulation duration is increased until the peak of the firstderivative of the evoked muscle response 120 exceeds a predeterminedthreshold (e.g., 0.1 mV/ms). If the proper stimulation duration isobtained, the algorithm proceeds from process step 148 to process step152. If a proper stimulation magnitude is not obtained, (i.e.,predetermined threshold not exceeded) the algorithm proceeds to processstep 150, in which indicator 66 is used to indicate a problem with thedetermination of stimulation magnitude to the user. Subsequently, thealgorithm returns to process step 140 and waits for reactivation of theSTART switch.

Upon determination of the proper stimulation magnitude, the algorithmproceeds with process step 152. In this step, the Median nerve 50 isstimulated at a predetermined rate (e.g., 2 Hz) for a predeterminedduration (e.g., 2 seconds). Each Thenar muscle response 120 is analyzed,as previously described, to estimate the distal motor latency (DML) asthe first major peak 133 of the second derivative 130 of the muscleresponse 120. Furthermore, the plurality of DML estimates are combinedto obtain a mean DML (m) and a standard deviation (s) about this mean.The algorithm then proceeds to process step 153 in which m and s areadjusted for variations in skin temperature. In particular, thefollowing two adjustment equations are applied:

    (A) m.sub.corrected =m.sub.uncorrected +k.sub.Ti +k.sub.2

    (B)S.sub.corrected =S.sub.uncorrected +k.sub.Ti +k.sub.2

The corrected mean DML (m_(corrected)) and standard deviation(s_(corrected)) represent the expected values at room temperature (i.e.,25° C. or 298° K.). The skin temperature, as measured by the temperaturesensor 36, is represented by the variable T. The values of constants k₁and k₂ are determined by a temperature calibration process. In thisprocess, multiple measurements of the mean DML are obtained at a varietyof temperatures spanning the expected range of temperatures over whichthe invention is normally used (e.g., 25° C. to 40° C.). Subsequently, alinear regression is performed between the temperatures and the mean DMLmeasurements. The constants k₁ and k₂ are determined directly from theregression coefficients.

The algorithm then continues with process step 154, in which thestandard deviation of the DML measurements, s, is compared against apredetermined threshold, s_(min). If s is larger or equal to s_(min),process step 156 is executed. Process step 156 evaluates the number oftimes m and s have been determined. If these values have been calculatedonly once, the algorithm returns to process step 146, wheredetermination of the proper stimulation level and all subsequentprocessing is repeated. If m and s have been determined twice, however,process step 158 is executed, resulting in indication of a diagnosticerror to the user through indicator 66. Subsequently, the algorithmreturns to process step 140 and waits for reactivation of the STARTswitch S1.

If in process step 154 it is determined that s is less than s_(min), thealgorithm proceeds with process step 160. In this step, the mean of theDML estimates, m, is compared against a first predetermined latencythreshold, t_(normal). If m is less than t_(normal), the algorithmproceeds to process step 162, in which a normal (i.e., user does nothave CTS) test result is indicated to user through indicator 66.Subsequently, the algorithm returns to process step 140 and waits forreactivation of the START switch S1. If m is greater or equal tot_(normal), the algorithm proceeds with process step 164, in which themean distal motor latency, m, is compared against a second predeterminedlatency value, t_(CTS). If m is greater than t_(CTS), the algorithmproceeds to process step 166, in which an abnormal (iLe., user has CTS)test result is indicated to user through indicator 66. Subsequently, thealgorithm returns to process step 140 and waits for reactivation of theSTART switch S1.

If neither of the two previous inequalities is true, the algorithmcontinues with process step 168. In this step, the Median nerve 150 isstimulated by pairs of electrical stimuli spaced apart at apredetermined temporal interval (e.g., 3 milliseconds). For each evokedmuscle response 120, the difference between the DML estimated from thefirst and second stimuli is determined. Furthermore, the plurality ofDML difference estimates are combined to obtain a mean DML difference(m') and a standard deviation (s') about this mean. Upon measurement ofthese two parameters, the algorithm proceeds to process step 170 inwhich the mean DML difference, m' is compared against a predeterminedthreshold, t_(shift). If m' is greater than t_(shift), process step 166is executed, in which an abnormal test result is indicated to the user,as described above. If this inequality does not hold, then an unknowntest result is indicated to user in process step 172. Subsequently, thealgorithm returns to process step 140 and waits for activation of theSTART switch S1.

The aforementioned algorithm is intended for illustrative purposes only.Other algorithms may be developed which detect CTS using an apparatus ofthe invention. For example, parameters other than the DML may beincorporated into the diagnostic algorithm. Illustrative parametersinclude: waveform features of the evoked muscle response 120, such as,for example, the amplitude and width. Additional illustrative parametersinclude waveform features of processed forms of the evoked muscleresponse 120, such as, for example, its derivatives, its Fouriertransform, and other parameters derived from statistical analyses (e.g.,principal component analysis). Furthermore, additional parameters areobtained by comparison of any of the above parameters at differentstimulation levels.

Although the illustrative algorithms described above pertain to thedetection of CTS, the apparatus of the present invention may used todetect other forms of nerve disease and to evaluate neuromuscularblockade. For example, the train-of-four (TOF) protocol, which iscommonly used to evaluate the degree of neuromuscular blockade inanesthetized patients, is readily implemented using an apparatus of theinvention. In particular, a predetermined number (usually four) ofmuscle responses 120 are evoked at a predetermined rate (e.g., 2 Hz) andthe amplitude 126 of each response determined. Subsequently, the ratioof the amplitude of the last of the plurality of muscle responses to beevoked is divided by the amplitude of the first of the plurality ofmuscle responses to be evoked. This ratio is recognized as a sensitiveindicator of neuromuscular blockade.

The disclosed invention provides a new approach to monitoringneuromuscular physiology. Apparatus and methods are described for thesubstantially automated and highly efficient measurement of manydifferent parameters of neuromuscular physiology. These indicators maybe used to detect Carpal Tunnel Syndrome (CTS) and other peripheralnerve diseases, as well as to monitor neuromuscular blockade caused bypathological, pharmacological and chemical means. The inventionpossesses the significant advantage that, unlike conventionalmeasurements of nerve conduction across the wrist, the disclosedinvention provides for a single integrated neuromuscular electrode thatis placed immediately proximal to the wrist (i.e., the wrist crease).This is a very familiar anatomic location and so the placement operationis rapidly and easily undertaken by most adults. Unlike apparatus andmethods of the prior art, the disclosed invention does not requireplacement of multiple sets of electrodes on both sides of the wrist,which is a difficult and error prone procedure for non-experts. Anadditional advantage of the disclosed invention emerges from the factthat the integrated neuromuscular electrodes may be manufactured as alow-cost, disposable item. Consequently, the possibility ofcross-contamination among users of the apparatus is significantlyreduced. Furthermore, the low-cost, and ease of use will promotefrequent monitoring of neuromuscular disorders, such as CTS, providingthe potential benefits of early detection and regular tracking of thedisease. Another advantage of the present invention is that the processof evoking, detecting and processing neuromuscular signals is carriedout in an entirely automated fashion, without requiring involvement ofeither the user of the apparatus or trained personnel. A furtheradvantage of the present invention is that the smallest and fewestelectrical stimuli consistent with an accurate diagnostic assessment areused. As a result, discomfort to the user is minimized and, in mostcases, eliminated entirely.

While the present invention has been described in terms of certainexemplary preferred embodiments, it will be readily understood andappreciated by one of ordinary skill in the art that it is not solimited, and that many additions, deletions and modifications to thepreferred embodiments may be made within the scope of the invention ashereinafter claimed. Accordingly, the scope of the invention is limitedonly by the scope of the appended claims.

What is claimed is:
 1. An apparatus for assessing a physiologicalfunction in an arm and a hand of an individual, comprising:(a) astimulator for producing a stimulus and for applying said stimulusproximal to a wrist of an individual, whereby application of saidstimulus stimulates a nerve that traverses said wrist; (b) a detectorfor detecting proximal to a wrist of an individual a myoelectricpotential, whereby said myoelectric potential is generated by a musclein a hand of said individual in response to said stimulus, said musclebeing in communication with said nerve; and (c) a controller forevaluating physiological function in response to said stimulus and saidmyoelectric potential.
 2. The apparatus of claim 1, wherein saidcontroller is further for determining a delay between application ofsaid stimulus and detection of said myoelectric potential and forproducing an indicia of said delay.
 3. The apparatus of claim 2, furthercomprising a temperature sensor in electrical communication with saidcontroller, said controller modifying said delay in response to saidtemperature.
 4. The apparatus of claim 2, further comprising anindicator in electrical communication with said controller and forreceiving said indicia from said controller and for indicating saiddelay in response to said indicia.
 5. The apparatus of claim 4, whereinsaid indicator comprises a light emitting diode.
 6. The apparatus ofclaim 2, wherein said controller is further for correlating said delayto said physiological function.
 7. The apparatus of claim 6, whereinsaid controller is adapted for producing a signal indicative of thepresence or absence of carpal tunnel syndrome in response to saidphysiological function.
 8. The apparatus of claim 7, further comprisingan indicator in electrical communication with said controller and forreceiving said signal from said controller and for indicating thepresence or absence of carpal tunnel syndrome in response to saidsignal.
 9. The apparatus of claim 1, wherein said stimulator comprises astimulation electrode for placement on said arm proximal to said wrist.10. The apparatus of claim 1, wherein said detector comprises adetection electrode for placement on said arm proximal to said wrist.11. The apparatus of claim 1, wherein said stimulus produced by saidstimulator is an electrical stimulus.
 12. The apparatus of claim 1,wherein said stimulus produced by said stimulator is a magneticstimulus.
 13. The apparatus of claim 1, further comprising acommunications port for establishing communication between saidcontroller and an external device, whereby said external device isadapted for evaluating and for indicating said physiological function inresponse to said stimulus and said myoelectric potential.
 14. A methodof assessing a physiological function in an arm and a hand of anindividual, comprising the steps of:(a) applying a stimulus proximal toa wrist of an individual whereby application of said stimulus stimulatesa nerve that traverses said wrist; (b) detecting a myoelectric potentialproximal to a wrist of an individual, whereby said myoelectric potentialis generated by a muscle in a hand of said individual in response tosaid stimulus, said muscle being in communication with said nerve; (c)processing said stimulus and said myoelectric potential; and (d)correlating said processing results to a physiological function of saidnerve and said muscle.
 15. The method of claim 14, wherein saidprocessing step further comprises the step of determining a delaybetween application of said stimulus and detection of said myoelectricpotential and said correlating step further comprises the step ofproducing an indicia of said delay.
 16. The method of claim 15, furthercomprising the step of indicating said delay in response to saidindicia.
 17. The method of claim 15, wherein said correlating stepfurther comprises the step of correlating said delay to saidphysiological function.
 18. The method of claim 17, further comprisingthe step of producing a signal indicative of the presence or absence ofcarpal tunnel syndrome in response to said physiological function. 19.The method of claim 18, further comprising the step of indicating thepresence or absence of carpal tunnel syndrome in response to saidsignal.
 20. The method of claim 16, wherein said step of determining adelay between application of said stimulus and detection of saidmyoelectric potential comprises the step of determining a secondderivative of said myoelectric potential.
 21. The method of claim 15,wherein said step of determining a delay between application of saidstimulus and detection of said myoelectric potential comprises the stepof determining a first derivative of said myoelectric potential.
 22. Themethod of claim 14, further comprising the steps of determining a firstderivative of said myoelectric potential and repeating steps (a) and (b)at incrementally increasing stimuli magnitudes until said firstderivative for one of said myoelectric potentials exceeds apredetermined level.
 23. The method of claim 14, further comprising thesteps of determining a delay between application of said stimulus anddetection of said myoelectric potential for at least two stimulusapplications, comparing the delays determined in response to applicationof each of said at least two stimulus applications and correlating saidcomparison to the presence or absence of carpal tunnel syndrome.